MULTI-CLADDING OPTICAL FIBER SCANNER
A multi-cladding optical fiber includes a core that conveys visible light used by a scanner for imaging a site within a patient's body, and an inner cladding that conveys high-power light, such as infrared light, used for providing therapy to site. The distal end of multi-cladding optical fiber is driven to scan the site when imaging or rendering therapy using an actuator. High-power light is coupled into inner cladding at proximal end of optical fiber using several different techniques. Some techniques use an axicon to direct the high-power light into the inner cladding, while visible light is coupled directly into the core. Another technique uses a multimode optical fiber in a coupling relationship with the multi-cladding optical fiber, to transfer high-power light from a core of the multimode fiber into the inner cladding of the multi-cladding optical fiber.
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The maximum transmissible optical power in a high-resolution scanning fiber endoscope system is limited by the requirement for small-core singlemode light propagation. The generally accepted threshold for material damage of a singlemode silica optical fiber is about 1 MW/cm2 for solid fiber and higher thresholds for photonics crystal or microstructured singlemode optical fibers. Thus, using an optical fiber that has a mode field diameter of 3.5 microns limits the optical power that can be delivered for therapy to a maximum of about 100 mW, when a conventional single resonant optical fiber is employed for both imaging and therapy. This level of power can easily be provided in the visible wavelengths by currently available diode-pumped solid-state or argon-ion gas lasers, and by high-power ultraviolet laser diodes and ultraviolet lasers that are being developed. Use of light in the visible range of wavelengths is desirable for rendering therapy in current configurations that employ the same optical fiber for both imaging and therapy, because of the potential for increased bending and launching losses that occur if infrared (IR) wavelengths are used in a visible wavelength optical fiber, or if shorter wavelength ultraviolet light is used in conventional multimode optical fiber scanners. Although tissue absorption levels are low in the visible range, it is expected that this amount of power will enable some limited therapeutic capability.
However, in the case where higher levels of optical power are needed for advanced levels of therapy, the existing scanning fiber endoscope design does not provide sufficient power handling capability. This problem only becomes an issue if it is necessary to both image and provide therapy to an internal site. If one or more fixed optical fibers are used to provide therapy, the nature and quantity of the therapeutic fibers and laser sources can be selected solely on the basis of therapeutic effect, with no regard to imaging. For example, the most commonly used laser in digestive endoscopy is the Nd:YAG laser which emits light at 1.06 micron wavelength that is usually conveyed to the tissues by a sheathed optical fiber within the working channel of the endoscope or within a cannula alongside the endoscope (Brunetaud, J. M., Maunoury, V., and Cochelard, D., Lasers in Digestive Endoscopy, Journal of Biomedical Optics 2(1): 42-52 January 1997). To deliver these much greater optical power levels, large-core multimode optical fibers would typically be used, rather than the small-core, singlemode optical fiber that is required for high-resolution imaging. To deliver more than fixed spots of laser irradiation to an imaged field, the separate large-core optical fiber(s) must be inserted through a larger endoscope within a working channel or secondary cannula that allows moving delivery of the optical therapeutic dosage across the stationary endoscopic field by hand. A drawback to this approach is that additional channels are required for combining imaging and therapy for minimally-invasive medicine.
One advantage of employing a dedicated fixed fiber configuration for a separate therapy channel is that it can operate at optical powers below the material damage threshold and still deliver sufficient power to perform a broad range of laser therapies. The disadvantage of such a configuration, however, is that the resulting endoscope system is more bulky and more invasive to the patient. Therefore, it would be desirable to provide a configuration for an endoscope system that can achieve maximal power operation in one single illumination fiber endoscope to provide the desired optical power therapeutic capacity, while also enabling imaging (and perhaps diagnostic) procedures to be conducted of the site to which the optical therapy is to be delivered. A compact single optical fiber endoscope with such properties has not yet been commercially available.
SUMMARYIn consideration of the preceding concerns, a relatively compact endoscopic apparatus has been developed for both imaging a site within a patient's body and rendering therapy to the site. An example of the most basic apparatus includes a dual-cladding optical fiber having a core, an inner cladding, and an outer cladding, all extending generally between a proximal end and a distal end. An imaging light source produces imaging light for use in illuminating a site within a patient's body, so that an image of the site can be viewed on a display screen. The imaging light is directed into the core of the dual-cladding optical fiber at the proximal end and is conveyed to the distal end of the dual-cladding optical fiber, where it is emitted toward the site to be imaged. A therapy light source is provided to produce therapy light having a substantially greater power than the imaging light. The therapy light is directed into the inner cladding at the proximal end and is conveyed to the distal end of the dual-cladding optical fiber, where it is used to render therapy to a desired region at a site. An actuator is disposed adjacent to the distal end of the dual-cladding optical fiber and is selectively energized so as to move the distal end of the core and the inner cladding in a desired path. When imaging the site, the moving distal end of the core is caused to move in the desired path so as to scan the site with the imaging light to illuminate it. Similarly, while rendering therapy to a desired region of the site, the moving inner cladding emits therapy light that is directed toward and over the desired region. At least one sensor is provided for receiving light from the site that is being imaged and produces a signal useful for creating an image of the site in response to the light received therefrom, for example, in response to the imaging light that is reflected from the site.
The apparatus of at least one embodiment further includes a housing disposed at the distal end of the dual-cladding optical fiber. The housing supports a lens system for focusing the imaging light and the therapy light emitted from the distal end of the dual-cladding optical fiber onto the site. Further, the at least one sensor can be disposed adjacent to the distal end of the dual-cladding optical fiber and supported by the housing to receive light from the site. In this case, the signal produced by the at least one sensor can be conveyed through at least one electrical lead that extends generally to the proximal end of the dual-cladding optical fiber.
Alternatively, at least one additional optical fiber can be included in the apparatus for conveying light received from the site toward the proximal end of the dual-cladding optical fiber. In this alternative embodiment, the at least one sensor is preferably disposed adjacent to the proximal end of the dual-cladding optical fiber and is coupled to the at least one additional optical fiber to receive the light from the site that was conveyed through the additional optical fiber.
In one form of the apparatus, an axicon is included for coupling the therapy light from the therapy light source into the inner cladding of the dual-cladding optical fiber, at the proximal end thereof, while enabling the imaging light from the imaging light source to be directed into the core of the dual-cladding optical fiber.
Other embodiments include a proximal lens system for focusing at least one of the therapy light (into the inner cladding), and the imaging light (into the core). In one embodiment, the proximal lens system includes a reflective surface. This reflective surface reflects either or both the therapy light (into the inner cladding), and the imaging light (into the core).
In yet another embodiment, an outer cladding is removed from a segment of the dual-cladding optical fiber adjacent to the proximal end, exposing the inner cladding within the segment. In this embodiment, the lens system directs the therapy light into the inner cladding at the segment, so that the therapy light is conveyed through the inner cladding toward the distal end of the dual-cladding optical fiber.
Still another embodiment includes a multimode optical fiber that is coupled to the therapy light source to receive the therapy light. The cladding is removed from a segment of the multimode optical fiber, exposing a multimode core that conveys the therapy light. An outer cladding is also removed from a segment of the dual-cladding optical fiber, exposing the inner cladding, but not disrupting the core. The inner cladding at this segment is also polished and affixed in contact with the multimode core that is polished, thereby facilitating transfer of the therapy light from the multimode core into the inner cladding. A fixture is preferably used to support the multimode core that is polished in a light coupling relationship with the inner cladding of the dual-cladding optical fiber that is polished.
Another embodiment includes a proximal lens system, and a reflective surface. The outer cladding and the inner cladding are removed from a segment of the dual-cladding optical fiber adjacent to the proximal end, forming a gap around the core. The reflective surface is then disposed in the gap, and the proximal lens system focuses the therapy light toward the reflective surface, which reflects the therapy light into an end of the inner cladding comprising one side of the gap. The therapy light is thus directed toward the distal end of the dual-cladding optical fiber within the inner cladding.
Another aspect of the present development is directed to a method for enabling imaging of a site within a patient's body and providing optical therapy to the site. The method includes steps that are generally consistent with the functionality of the elements in the different embodiments of the apparatus discussed above.
This Summary has been provided to introduce a few concepts in a simplified form that are further described in detail below in the Description. However, this Summary is not intended to identify key or essential features of the claimed subject matter, nor is it intended to be used as an aid in determining the scope of the claimed subject matter.
Various aspects and attendant advantages of one or more exemplary embodiments and modifications thereto will become more readily appreciated as the same becomes better understood by reference to the following detailed description, when taken in conjunction with the accompanying drawings, wherein:
Exemplary embodiments are illustrated in referenced Figures of the drawings. It is intended that the embodiments and Figures disclosed herein are to be considered illustrative rather than restrictive.
Exemplary Scanning DeviceAn exemplary optical fiber device 10, which is drivable in a variable linear or elliptical scan mode and is useful for both imaging an internal site and rendering therapy to the internal site as discussed below, is illustrated in
An image is generated by the fiber scanner shown in
As illustrated in
A cut-away view in
A series of variable radii circles are produced in a circular scan mode. The optical fiber can be driven in either mode during successive scanning frames. When driven in a spiral scan mode, the optical fiber produces a spiral scan in which the radius alternately increases and decreases. In an alternative scan pattern, the radius is increased in the desired pattern, and then the fiber is more rapidly returned to its centered position to begin the next frame. In either the circular or spiral scan modes, the distal end of optical fiber 208 scans an ROI to image the region and also renders therapy and/or diagnostic functions to the ROI. The whirling motion of the cantilevered optical fiber is controllably driven larger or smaller in diameter by increasing or decreasing the voltage applied to the four individual quadrants of piezoceramic tube actuator 206. Changes in the diameter of the scan can thus be made in successive scanning frames. When imaging an adjacent site within a patient's body, the diameter of the scan may be made greater to encompass a larger area in one scan frame, and in a subsequent scanning frame, can be reduced, when rendering therapy only to a small portion of the imaged area.
Exemplary Scanning SystemExternally, the illumination optics and scanner(s) are supplied light from imaging sources and modulators as shown in a block 156. Further details concerning several preferred embodiments of external light source systems 158 for producing RGB, UV, IR, and high-intensity light conveyed to the distal end of an optical fiber system are either disclosed below or will be evident to a person of ordinary skill in this art. Scanner sensors can be used for controlling the scanning and produce a signal that is fed back to the scanner actuators, illumination source, and modulators to implement the scanning control after signal processing in a block 168.
In block 160, image signal filtering, buffering, scan conversion, amplification, and other processing functions are implemented using the electronic signals produced by the imaging photon detectors and for the other photon detectors employed for diagnosis/therapy, and monitoring purposes. Blocks 156 and 160 are interconnected bi-directionally to convey signals that facilitate the functions performed by each respective block. Similarly, each of these blocks is bi-directionally coupled in communication with a block 162 in which analog-to-digital (A/D) and digital-to-analog (D/A) converters are provided for processing signals that are supplied to a computer workstation user interface or other computing device employed for image acquisition, processing, for executing related programs, and for other functions. Control signals from the computer workstation are fed back to block 162 and converted into analog signals, where appropriate, for controlling or actuating each of the functions provided in blocks 156, 158, and 160. The A/D converters and D/A converters within block 162 are also coupled bi-directionally to a block 164 in which data storage is provided, and to a block 166. Block 166 represents a user interface for maneuvering, positioning, and stabilizing the end of the scanning optical fiber within a patient's body.
In block 164, the data storage is used for storing the image data produced by the detectors within a patient's body, and for storing other data related to the imaging and functions implemented by the scanning optical fiber. Block 164 is also coupled bi-directionally to the computer workstation 168 and to interactive display monitor(s) in a block 170. Block 170 receives an input from block 160, enabling images of the ROI to be displayed interactively. In addition, one or more passive video display monitors may be included within the system, as indicated in a block 172. Other types of display devices 174, for example, a head-mounted display (HMD) system, can also be provided, enabling medical personnel to view an ROI as a pseudo-stereo image.
Dual-Cladding Optical FiberDetails of an exemplary dual-cladding optical fiber 250 are illustrated in
An additional outer cladding layer 258 is shown on an exemplary multi-cladding (in this example, a triple-cladding) optical fiber 250′ in
Coupling Both Visible and High-intensity Light into Dual-Cladding Optical Fiber
Several different exemplary embodiments have been developed for coupling visible light used for imaging into the small diameter core of a dual-cladding optical fiber, and substantially higher power light used for therapy into the inner cladding of the dual-cladding optical fiber. For example,
Both the laser source of high-power NIR light for therapy and the visible light source for imaging are disposed externally of a patient, adjacent to a proximal end of dual-cladding optical fiber 250. Visible light 276 and NIR light 278 are combined into a single beam of light by using a dichroic beamsplitter 279 positioned at a 45-degree angle (e.g., the visible light is reflected by the beamsplitter, while the NIR light is transmitted through it). In one case, the two beams are collimated before being combined and then directed to a lens 282. The lens has chromatic aberration such that the visible wavelength light has a shorter focal length than the NIR light. As a result, visible light 276 is directed by the lens into core 252 of dual-cladding optical fiber 250, while NIR light 278 is directed by the lens into inner cladding 254 of the dual-cladding optical fiber. In a second case (not shown) the visible light is provided as a slightly converging beam, while the NIR light is provided as a slightly diverging beam, before being combined. The different degrees of collimation of the visible and NIR light result in different focal points from lens 282, with the visible light focusing nearer and the NIR light focusing farther from lens 282. In a third case (also not shown), the visible light is directed toward the center of lens 282, while the NIR light is directed to a radially outer portion of the lens. Due to first order optical aberration, such as spherical aberration, the focal points of the two beams of light are spatially displaced, so that the NIR light is focused into the inner cladding, while the visible light is focused into the core of the dual-cladding optical fiber.
An exemplary embodiment 288 for coupling the high-power NIR light and visible light into a dual-cladding optical fiber is illustrated in
In
As a variation (not shown), axicon 298 can be replaced with a regular prism that is fused to one side of dual-cladding optical fiber 250 in place of axicon 298, proximal of gap 300, so that NIR light from lens 282 is similarly directed by the prism into inner cladding 254, which is exposed at gap 300. It should also be understood that the diameter of singlemode optical fiber 294 could be substantially reduced (compared to what is shown in
Yet another technique for coupling NIR light into inner cladding 254 employs coupling between optical fibers to add high-power NIR for therapy into the inner cladding of a dual-cladding optical fiber.
In this embodiment, optical fiber 350 is a multimode optical fiber having a core 354 with the same dimensions and optical properties as the inner cladding of dual-cladding optical fiber 250. These two optical fibers are coupled together along a coupling section 352. The high-intensity light being conveyed through the core of the multimode optical fiber is thus coupled into the inner cladding of the dual-cladding optical fiber where the two are in contact with each other at coupling section 352.
Further details of coupling section 352 are illustrated in the cross-section shown in
The polished flattened portions of the dual-clad and multimode optical fibers are then brought into contact, aligned, and fixed in place with mounting holder 370. An adhesive is applied to the facing surfaces or bonding pads 376 of the upper block and the lower block, which are thus held together, forming mounting holder 370, as shown in
Although the concepts disclosed herein have been described in connection with the preferred form of practicing them and modifications thereto, those of ordinary skill in the art will understand that many other modifications can be made thereto within the scope of the claims that follow. Accordingly, it is not intended that the scope of these concepts in any way be limited by the above description, but instead be determined entirely by reference to the claims that follow.
Claims
1. A method for enabling imaging of a site within a patient's body and providing optical therapy to the site, comprising the steps of:
- (a) conveying imaging light from an imaging light source through a core of a multi-cladding optical fiber from a proximal end of the multi-cladding optical fiber to a distal end thereof;
- (b) driving the distal end of the multi-cladding optical fiber to scan the site;
- (c) detecting light from the site resulting from scanning the site with the imaging light, and in response to detecting the light, producing a signal used to create an image of the site;
- (d) conveying therapy light through an inner cladding of the multi-cladding optical fiber from a therapy light source disposed external to the patient's body, to the distal end of the multi-cladding optical fiber, the therapy light having a substantially higher power than the imaging light; and
- (e) selectively scanning the distal end of the multi-cladding optical fiber to direct the therapy light toward a desired region at the site.
2. The method of claim 1, further comprising the step of focusing the imaging light and the therapy light emitted from the distal end of the multi-cladding optical fiber onto the site.
3. The method of claim 1, wherein the step of detecting comprises the step of detecting light with at least one sensor disposed adjacent to the distal end of the multi-cladding optical fiber, the at least one sensor producing the signal that is conveyed through an electrical conductor to the proximal end of the multi-cladding optical fiber and used to produce an image of the site.
4. The method of claim 1, wherein the step of detecting comprises the steps of:
- (a) conveying the light from the site through at least one additional optical fiber toward the proximal end of the multi-cladding optical fiber; and
- (b) detecting light with at least one sensor disposed external to the patient's body, the at least one sensor producing the signal that is used to produce the image of the site.
5. The method of claim 1, wherein the step of driving the distal end of the multi-cladding optical fiber comprises the step of energizing an actuator disposed proximate to the distal end of the multi-cladding optical fiber, the actuator causing the core and inner cladding of the multi-cladding optical fiber to move in a desired pattern so that the imaging light emitted from the distal end of the core of the optical fiber scans the site in the patient's body.
6. The method of claim 5, wherein the step of selectively scanning comprises the step of selectively energizing the actuator with a drive signal to move the inner cladding and core in a desired pattern, to direct the therapy light toward the desired region at the site.
7. The method of claim 1, further comprising the step of separately coupling the imaging light from the imaging light source and the therapy light from the therapy light source into the multi-cladding optical fiber, so that the imaging light is directed into a proximal end of the core and the therapy light is directed into the inner cladding of the multi-cladding optical fiber.
8. The method of claim 7, wherein the step of coupling comprises the step of directing the therapy light through an axicon so as to transmit the therapy light into the inner cladding of the multi-cladding optical fiber.
9. The method of claim 7, wherein the step of coupling comprises the steps of:
- (a) removing an outer cladding along a portion of a multimode optical fiber to expose a segment of a multimode core;
- (b) removing an outer cladding along a portion of the multi-cladding optical fiber to expose a segment of the inner cladding;
- (c) polishing the segments of the multimode core and the inner cladding that were exposed;
- (d) affixing the segment of the multimode core that was polished in contact with the segment of the inner cladding that was polished, coupling the multimode core in light communication with the inner cladding; and
- (e) directing the therapy light into an end of the multimode core so that the therapy light is coupled into the inner cladding of the multi-cladding optical fiber.
10. The method of claim 7, wherein the step of coupling comprises the steps of:
- (a) removing an outer cladding from a proximal segment of the multi-cladding optical fiber, to expose the inner cladding at the proximal segment; and
- (b) directing the therapy light from the therapy light source into the inner cladding at the proximal segment, so that the therapy light is conveyed through the inner cladding toward the distal end of the multi-cladding optical fiber.
11. The method of claim 7, wherein the step of coupling comprises the steps of:
- (a) removing an outer cladding and the inner cladding from a proximal segment of the multi-cladding optical fiber to form a gap in the outer cladding and the inner cladding around the core, at the proximal segment; and
- (b) directing the therapy light from the therapy light source toward the gap and into an adjacent end of the inner cladding comprising one side of the gap, so that the therapy light travels toward the distal end of the multi-cladding optical fiber.
12. Apparatus for imaging a site within a patient's body and rendering therapy to a site, comprising:
- (a) a multi-cladding optical fiber that includes a core, an inner cladding, and an outer cladding, all extending generally between a proximal end and a distal end of the multi-cladding optical fiber;
- (b) an imaging light source that produces an imaging light for use in illuminating a site within a patient's body to produce an image of a site, the imaging light being directed into the core of the multi-cladding optical fiber at the proximal end and being conveyed to the distal end of the multi-cladding optical fiber, for emission toward a site to be imaged;
- (c) a therapy light source that produces therapy light having a substantially greater power than the imaging light, the therapy light being directed into the inner cladding at the proximal end and being conveyed to the distal end of the multi-cladding optical fiber, to render therapy to a desired region at a site;
- (d) an actuator disposed adjacent to the distal end of the multi-cladding optical fiber, the actuator being selectively energized so as to move the distal end of the core and the inner cladding in a desired path, both while imaging a site using the imaging light to illuminate and while rendering therapy to a desired region of a site with the therapy light emitted from the inner cladding and directed toward the desired region; and
- (e) at least one sensor for receiving light from a site that is being imaged, the at least one sensor producing a signal useful for producing an image of a site in response to the light received therefrom as a result of the imaging light illuminating a site.
13. The apparatus of claim 12, further comprising a housing disposed at the distal end of the multi-cladding optical fiber, the housing supporting a lens system for focusing the imaging light and the therapy light emitted from the distal end of the multi-cladding optical fiber onto a site.
14. The apparatus of claim 13, wherein the at least one sensor is disposed adjacent to the distal end of the multi-cladding optical fiber and supported by the housing to receive light, the signal produced by the at least one sensor being conveyed through at least one electrical lead that extends generally to the proximal end of the multi-cladding optical fiber.
15. The apparatus of claim 12, further comprising at least one additional optical fiber for conveying light received from a site toward the proximal end of the multi-cladding optical fiber, wherein the at least one sensor is disposed adjacent to the proximal end of the multi-cladding optical fiber and is coupled to the at least one additional optical fiber.
16. The apparatus of claim 12, further comprising an axicon for coupling the therapy light from the therapy light source into the inner cladding of the multi-cladding optical fiber, enabling the imaging light from the imaging light source to be directed into the core of the multi-cladding optical fiber, at the proximal end thereof.
17. The apparatus of claim 16, further comprising a proximal lens system for focusing at least one of the therapy light into the inner cladding, and the imaging light into the core.
18. The apparatus of claim 17, wherein the proximal lens system includes a reflective surface that reflects at least one of the therapy light into the inner cladding, and the imaging light into the core.
19. The apparatus of claim 17, wherein an outer cladding is removed from a segment of the multi-cladding optical fiber adjacent to the proximal end, exposing the inner cladding within the segment, and wherein the lens system directs the therapy light into the inner cladding at the segment, so that the therapy light is conveyed through the inner cladding toward the distal end of the multi-cladding optical fiber.
20. The apparatus of claim 12, further comprising a multimode optical fiber that is coupled to the therapy light source to receive the therapy light, an outer cladding being removed from the multimode optical fiber along a segment thereof, exposing a multimode core that conveys the therapy light, the multimode core that is exposed being polished, wherein an outer cladding is also removed from a segment of the multi-cladding optical fiber, exposing the inner cladding, the inner cladding at the segment also being polished and affixed in contact with the multimode core that is polished to facilitate transfer of the therapy light from the multimode core into the inner cladding, so that the therapy light can be conveyed through the inner cladding toward the distal end of the multi-cladding optical fiber.
21. The apparatus of claim 20, further comprising a fixture to support the multimode core that is polished in a light coupling relationship with the inner cladding that is polished.
22. The apparatus of claim 12, further comprising a proximal lens system that includes a reflective surface, wherein the outer cladding and the inner cladding are removed from a segment of the multi-cladding optical fiber adjacent to the proximal end, forming a gap around the core in which the reflective surface is disposed, the proximal lens system focusing the therapy light toward the reflective surface so that the therapy light is reflected therefrom and into an end of the inner cladding comprising one side of the gap, the therapy light thus being directed toward the distal end of the multi-cladding optical fiber within the inner cladding.
23. An endoscopic system for illuminating an internal site with visible light and rendering a therapy to the internal site within a patient's body with a relatively high-power light, comprising:
- (a) a high-power light source that produces high-power light for rendering the therapy;
- (b) a visible light source, the visible light source producing visible light that is substantially lower in power than the high-power light, and is employed for illuminating an internal site;
- (c) a multi-cladding optical fiber that includes an outer cladding, an inner cladding, and a core;
- (d) an actuator that is selectively energized to move a cantilevered portion of the core and the inner cladding in a desired pattern proximate to an internal site, so that visible light emitted from the core scans and illuminates the internal site to enable imaging of the internal site, and so that high-power light emitted from the inner cladding scans over a desired region of the internal site to render therapy to the desired region;
- (e) first means for coupling the high-power light into the inner cladding of the multi-cladding optical fiber, the inner cladding conveying the high-power light toward an internal site; and
- (f) second means for coupling the visible light into the core of the multi-cladding optical fiber, the core conveying the visible light toward the internal site.
24. The endoscopic system of claim 23, further comprising at least one optical sensor for responding to visible light reflected from an internal site, to produce a signal useful for creating an image of the internal site.
25. The endoscopic system of claim 24, wherein the at least one optical sensor is disposed on a housing configured to be advanced to an internal site, the optical sensor being coupled to at least one electrical lead for conveying the signal externally of the internal site.
26. The endoscopic system of claim 24, further comprising at least one optical fiber that conveys the visible light reflected from an internal site externally of the internal site, to the at least one optical sensor.
27. The endoscopic system of claim 23, further comprising an internal lens system that directs and focuses the visible light and the high-power light at an internal site.
28. The endoscopic system of claim 23, wherein the first means comprises a lens system for directing and focusing the high-power light into the inner cladding.
29. The endoscopic system of claim 28, wherein the lens system comprises at least one axicon that is configured to direct the high-power light into the inner cladding.
30. The endoscopic system of claim 29, wherein the outer cladding is removed along a section of the multi-cladding optical fiber, exposing the inner cladding within the section, and wherein the at least one axicon directs the high-power light into the inner cladding that is exposed within the section, so that the high-power light is conveyed through the inner cladding toward an internal site.
31. The endoscopic system of claim 30, wherein the second means for coupling comprises a multimode optical fiber having one end coupled to the source of the visible light to convey the visible light within a core of the multimode optical fiber, and another end coupled to the multi-cladding optical fiber proximal of the section where the outer cladding is removed, so that the core of the multimode optical fiber abuts the core of the multi-cladding optical fiber and transmits the visible light into the core of the multi-cladding optical fiber.
32. The endoscopic system of claim 28, wherein both the outer cladding and the inner cladding are removed from a section of the multi-cladding optical fiber, forming a gap around the core, and wherein the lens system comprises a reflector disposed within the gap and angled to reflect the high-power light into an end of the inner cladding that comprises one side of the gap.
33. The endoscopic system of claim 23, wherein the first means for coupling comprises a multimode optical fiber that is coupled to the high-power light source and which conveys the high-power light from the high-power source, and a fixture that couples an exposed and polished section of a multimode core of the multimode optical fiber in light communication with an exposed and polished section of the inner cladding of the multi-cladding optical fiber, so that the high-power light being conveyed through the multimode optical fiber enters the inner cladding and is conveyed to an internal site.
34. The endoscopic system of claim 23, wherein the second means for coupling comprises a singlemode optical fiber having one end coupled to the visible light source to receive and convey the visible light and an opposite end coupled to the core of the multi-cladding optical fiber to receive the visible light for transmission to an internal site.
35. The endoscopic system of claim 23, wherein the second means for coupling comprises a reflector disposed to direct light received from the visible light source into the core of the multi-cladding optical fiber for transmission to an internal site.
Type: Application
Filed: Mar 3, 2006
Publication Date: Jan 22, 2009
Patent Grant number: 9561078
Applicant: University of Washington (Seattle, WA)
Inventors: Eric Seibel (Seattle, WA), Richard Johnston (Sammamish, WA), Charles David Melville (Issaquah, WA)
Application Number: 12/281,251
International Classification: A61B 1/07 (20060101); G02B 6/06 (20060101); A61N 5/06 (20060101); A61B 6/00 (20060101);